Algorithm for breathing efficiency

ABSTRACT

A method of determining a fitness level of user with an acoustic measurement device configured to measure sound associated with airflow through a mammalian trachea. The acoustic measurement device is in communication with a controller having processing circuitry. The method includes correlating the measured sound into a measurement of the user&#39;s respiratory rate and tidal volume; calculating a second respiratory rate value using the measured tidal volume; calculating a breathing efficiency (BE) ratio based on a comparison of the user&#39;s measured respiratory rate and the calculated second respiratory rate value; correlating the calculated BE ratio to a predetermined threshold; and assigning a classification to the user based on the calculated BE ratio. The classification is indicative of the user&#39;s respiratory function performance.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims the benefit of U.S. Application Ser. No.63/217,487, filed Jul. 1, 2021.

TECHNICAL FIELD

This disclosure relates to a method and system for a method ofdetermining a respiratory fitness level of a user with diagnosticalgorithms that quantify and analyze the pattern of the user'srespiratory rate (RR), tidal volume (TV), and breathing efficiency (BE),among other physiological conditions.

BACKGROUND

Existing health, wellness, and fitness systems generally trackphysiological parameters such as heart rate, blood pressure, bodytemperature, etc. These physiological parameters may be tracked andrelayed to a user via a smart device, such as a smart phone and/or asmart watch. Because smart watches are generally secured around a user'swrist or arm during exercise, they commonly include at least one sensorthat is configured to be in contact with the user's skin to monitor thewearer's physiological parameters. However, because these smart watchesand/or smart phones are not located proximate to the user's chest,throat, or mouth, they are unable to accurately monitor respiratoryparameters such as respiratory rate and tidal volume of the user duringexercise. Thus, this information is often not available to usersfollowing the completion of an exercise routine or physical activity.

Monitoring various respiratory values including breathing frequency,breathing effort, tidal volume and other related respiratory values canhelp monitor and interpret the health and well-being of an individual.Vital signs, such as respiration, are often overlooked, poorlydocumented, and undervalued in the clinical setting. Monitoring andinterpreting various respiratory values can help to improve theunderstanding of respiratory physiology and clinical assessments.Respiratory rates can be an indicator of certain clinical deteriorationswhich often occur before other vital sign changes are detectible. Thistype of respiratory information can be used to improve the safety andoutcomes of individuals based upon their respiratory values.

SUMMARY

The techniques of this disclosure generally relate to a method, device,and system for determining fitness levels.

In one aspect, a method of determining a fitness level of user with anacoustic measurement device configured to measure sound associated withairflow through a mammalian trachea. The acoustic measurement device isin communication with a controller having processing circuitry. Themethod includes correlating the measured sound into a measurement of theuser's respiratory rate and tidal volume; calculating a secondrespiratory rate value using the measured tidal volume; calculating abreathing efficiency (BE) ratio based on a comparison of the user'smeasured respiratory rate and the calculated second respiratory ratevalue; correlating the calculated BE ratio to a predetermined threshold;and assigning a classification to the user based on the calculated BEratio. The classification is indicative of the user's respiratoryfunction performance.

In another aspect, the acoustic measurement device includes at least onesound transducer, the at least one sound transducer being configured tomeasure the sound associated with airflow through the mammalian trachea.

In another aspect, the assigned classification is one selected from thegroup consisting of an elite athlete level, a trained athlete level, anda lesser athlete level.

In another aspect, the elite athlete level classification is assignedwhen the BE ratio is greater than the predetermined threshold. Thetrained athlete level classification is assigned when the BE ratio isequal to the predetermined threshold. The lesser athlete levelclassification is assigned when the BE ratio is less than thepredetermined threshold.

In another aspect, the elite athlete level has a BE>1.0, the trainedathlete level has a BE=1.0, and the lesser athlete level has a BE<1.0.

In another aspect, the measurement of sound associated with airflowthrough the trachea occurs at least one from the group consisting ofperiodically, intermittently, and continuously.

In another aspect, the acoustic measurement device includes a housing,and the at least one sound transducer may be suspended within thehousing.

In another aspect, the housing of the acoustic measurement device has awidth between 0.5 cm and 3.5 cm.

In another aspect, the acoustic measurement device is in wirelesscommunication with the controller.

In another aspect, the controller is a smart device.

In another aspect, the method further comprises filtering out a set ofanomalous data and ambient noise from the measured sound vibrations.

In another aspect, the second respiratory rate value is calculated usingthe measured tidal volume with a first equation for men and a secondequation for women, the first equation beingRR2=8.3465e^(0.7458(tidal volume)) and the second equation beingRR2=9.6446e^(0.9328(tidal volume)).

In one aspect, a method of determining a fitness level of a user with anacoustic measurement device at least one of before, during, or afterphysical activity. The acoustic measurement device includes a soundtransducer configured to measure sound associated with airflow through amammalian trachea. The method comprising correlating the measured soundinto a measurement of the user's respiratory rate and tidal volume at apredetermined time interval; calculating a second respiratory rate valueusing the measured tidal volume; calculating a breathing efficiency (BE)ratio based on a comparison of the user's measured respiratory rate andthe calculated second respiratory rate value; correlating the calculatedBE ratio to a predetermined threshold; and assigning a classification tothe user based on the calculated BE ratio. The classification may be oneselected from the group consisting of: an elite athlete level, a trainedathlete level, and a lesser athlete level.

In another aspect, the elite athlete level classification is assignedwhen the BE ratio is greater than the predetermined threshold, thetrained athlete level classification is assigned when the BE ratio isequal to the predetermined threshold, and the lesser athlete levelclassification is assigned when the BE ratio is less than thepredetermined threshold.

In another aspect, the measurement of sound associated with airflowthrough the trachea occurs at least one from the group consisting ofperiodically, intermittently, and continuously.

In another aspect, the acoustic measurement device includes a housingand a sound transducer, and wherein the sound transducer is suspendedwithin the housing.

In another aspect, the housing of the acoustic measurement device has awidth between 0.5 cm and 3.5 cm.

In another aspect, the acoustic measurement device is in communicationwith a controller configured, the controller being configured tocorrelate the measured sound into the measurement of the user'srespiratory rate and tidal volume at a predetermined time interval,calculate the second respiratory rate value using the measured tidalvolume, calculate the breathing efficiency (BE) ratio based on thecomparison of the user's measured respiratory rate and the calculatedsecond respiratory rate value, correlate the calculated BE ratio to thepredetermined threshold, and assign the classification to the user basedon the calculated BE ratio, the classification being one selected fromthe group consisting of the elite athlete level, the trained athletelevel, and the lesser athlete level.

In another aspect, the controller is a smart device.

In another aspect, the method further comprises filtering out a set ofanomalous data and ambient noise from the measured sound vibrations.

In another aspect, the method further comprises a housing, the housingis configured to releasably couple to skin of the mammalian trachea byan adhesive or an adjustable band.

In one aspect, a method of determining a fitness level of a user with anacoustic measurement device at least one of before, during, or afterphysical activity. The acoustic measurement device including a soundtransducer configured to measure sound associated with airflow through amammalian trachea the acoustic measuring device being in communicationwith a controller configured to perform the method. The methodcomprising correlating the measured sound into a measurement of theuser's respiratory rate and tidal volume at a predetermined timeinterval; calculating a second respiratory rate value using the measuredtidal volume; calculating a breathing efficiency (BE) ratio based on acomparison of the user's measured respiratory rate and the calculatedsecond respiratory rate value for a predetermined point in time or overa predetermined period of time; correlating the calculated BE ratio to apredetermined threshold; and assigning a classification to the userbased on the calculated BE ratio. The classification being one selectedfrom the group consisting of an elite athlete level where thisclassification is assigned when the BE ratio is greater than thepredetermined threshold, a trained athlete level where thisclassification is assigned when the BE ratio is equal to thepredetermined threshold, and a lesser athlete level where thisclassification is assigned when the BE ratio is less than thepredetermined threshold.

BRIEF DESCRIPTION OF THE DRAWINGS

A more complete understanding of embodiments described herein, and theattendant advantages and features thereof, will be more readilyunderstood by reference to the following detailed description whenconsidered in conjunction with the accompanying drawings wherein:

FIG. 1 is a cross-sectional view of embodiment of an acoustic sensorconstructed in accordance with the principles of the present applicationand a view of the acoustic sensor coupled to a patient's body;

FIG. 2 is a cross-sectional view of another embodiment of an acousticsensor constructed in accordance with the principles of the presentapplication;

FIG. 3 is a cross-sectional view of another embodiment of an acousticsensor constructed in accordance with the principles of the presentapplication;

FIG. 4 is a cross-sectional view of another embodiment of an acousticsensor constructed in accordance with the principles of the presentapplication;

FIG. 5 is a cross-sectional view of another embodiment of an acousticsensor constructed in accordance with the principles of the presentapplication;

FIG. 6 is another a cross-sectional view of embodiment of an acousticsensor constructed in accordance with the principles of the presentapplication; and

FIG. 7 is a flow chart showing exemplary steps of determining a user'srespiratory function performance level before, during or after exercise,an athletic or fitness performance test, or other form of physicalactivity in accordance with an embodiment of the present application.

DETAILED DESCRIPTION

Before describing in detail exemplary embodiments, it is noted that theembodiments reside primarily in combinations of apparatus components andprocessing steps related to a method and system for determining arespiratory fitness level of a user with diagnostic algorithms thatquantify and analyze the pattern of the user's respiratory rate (RR),tidal volume (TV), and breathing efficiency (BE), among otherphysiological conditions. The measurements including the RR, TV, BE, andother physiological measurements which are made using the method andsystems may be continuously monitored, may be averaged over a period oftime which may correspond to, for example, an exercise period, aphysical/fitness performance evaluation period, or may be made for anyother preset time interval. Accordingly, the system and methodcomponents have been represented where appropriate by conventionalsymbols in the drawings, showing only those specific details that arepertinent to understanding the embodiments of the present disclosure soas not to obscure the disclosure with details that will be readilyapparent to those of ordinary skill in the art having the benefit of thedescription herein.

With reference to FIGS. 1-7 , an acoustic measurement device such as,for example, a Tracheal Sound Sensor (TSS) 10, is depicted which issized and configured to be releasably affixed to the skin of a mammal oruser by an adhesive or adjustable elastic band. As described herein, inone embodiment the TSS 10 of the present invention may be configuredsimilarly to the acoustic measurement device as set forth in U.S. Pat.No. 11,000,191, issued on May 11, 2021, and entitled “ACOUSTIC SENSORAND VENTILATION MONITORING SYSTEM,” which is incorporated herein byreference. The TSS 10 includes a housing 12 defining an at leastpartially enclosed chamber 14 therein. In one configuration, the housing12 defines a width and a length of approximately 3.5 cm or less. Forexample, the housing 12 may be substantially cube shaped having a widthof 3.5 cm or less, such as between 0.5 cm to 3.5 cm, a sphere or dischaving a diameter of 3.5 cm or less, or another shape suitable foraffixing to the user, including but not limited to an oval, a rectangle,or any other configuration.

The housing 12 may be composed of one or more materials, such as alightweight plastic, metal, ceramic, or composite having integrated oradded sound insulation material 16 on an exterior thereof, lining theinterior of the chamber, or both, to attenuate ambient sound.Additionally, other active and passive noise cancellation techniques maybe used as well, including additional sound transducers. For example,additional microphones and/or acoustic sensors may be added to the TSS10to provide active noise cancellation. Additionally and/or alternatively,sound insulation materials may be added to the TSS 10 to provide passivenoise cancellation. Software may also be included in the TSS 10 toactively remove any noise from the respiratory data as well. The wallsof the housing and lining may be separated by an air-filled spacedesigned to attenuate ambient sound. The housing 12 may be manufacturedfrom materials and structure that attenuates transmission of ambientsound into the chamber 14. In one configuration, an airtight seal isformed between the housing 12 and skin surface to isolate the inside ofthe TSS 10 from the external environment. In an alternativeconfiguration, the housing 12 may be porous or have an external openingsuch that sound may penetrate the housing 12 from an ambientenvironment, depending on the application. In one configuration, thehousing 12 defines a single opening 18 to provide access to the chamber14, however, the number and size of the openings 18 are not limited to aparticular number and size. The sound insulation material 16 maysurround the housing 12 in all areas with the exception of around theopening 18. The housing 12 may define a dome shape, a bell shape, or anyshape such that the chamber 14 is isolated from external sounds andoptimized to measure the sounds of air movement within the trachea.

One or more sound transducers 20 may be affixed, either permanently orremovably, within the chamber 14 of the housing 12 for measuring atleast one of a respiratory rate and a tidal volume of the patient. Thesound transducer 20 may be one or more microphones, for example, in the20-2000 Hz range, configured to measure sound energy within the chamber14 and transduce an acoustic signal into a digital signal. The miniatureelectronic microphones (electric, piezoelectric, or MEMS) transduce themechanical vibrations caused by airflow within the proximal tracheaduring inhalation and exhalation with a high signal-to-noise ratio. Inone configuration, the sound transducer 20 is located at an end of thehousing 12 opposite an end of the housing 12 defining the opening 18 andmay be suspended within the chamber 14 using, for example, an elongaterod or other suspension element (not shown) extending from the interiorsurface of the chamber 14 such that the sound transducer 20 is not incontact with the interior walls of the housing 12.

A flexible diaphragm 22 may be disposed within the opening 18 that iscoextensive or slightly recessed within a surface of the housing 12. Thediaphragm 22 may be a thin flexible material that resonates in responseto sound energy, for example airflow through the trachea of a mammal, ina manner similar to a pediatric stethoscope head. In one configuration,the diaphragm 22 is electrically coupled to the sound transducer 20 suchthat when the diaphragm 22 resonates, the sound vibration is directlymeasured by the sound transducer 20. In other configurations, ratherthan being coupled to the diaphragm 22, the sound transducer 20 is inclose proximity to the diaphragm 22, for example, immediately adjacentthereto to minimize any ambient sound measured by the sound transducer20. In other configurations, the diaphragm 22 is the actual diaphragm ofthe sound transducer 20 and is directly coupled to an electromagneticcoil, capacitor, or piezoelectric crystal of the sound transducer 20. Inone configuration, the interior of the housing 12 may define a curvedsemi-circle, dome, or other shape to focus the sound energy transducedfrom the diaphragm 22 on the skin surface directly into the soundtransducer 20. For example, the sound transducer 20 and diaphragm 22 maybe angled and positioned in a manner to measure sounds of the airflow asit enters and exits the larynx. In other configurations, the soundtransducer 20 and the diaphragm 22 are aimed toward the airflow throughthe trachea. In one configuration, the sound transducer 20 is apiezoelectric film with adhesive that adheres to the skin surfaceadjacent or proximal to the trachea.

Continuing to refer to FIGS. 1-6 , a wireless transmitter 24 may becoupled to the housing 12, which is in communication with the soundtransducer 20. The wireless transmitter 24, which may transmit andreceive, is configured to transmit the transduced acoustic signalmeasured by the sound transducer 20. In one configuration, the wirelesstransmitter 24 is included as part of a processing circuitry having oneor more processors included within the housing 12. For example, thewireless transmitter 24 may transmit the measurement of the respiratoryrate, the tidal volume, the heart rate, or other vital sign data, to acontroller 26 which forms an acoustic ventilation monitoring system(AVMS) 27 in combination with the TSS 10. In one embodiment, thecontroller 26 may be a remote controller in the form of a smartphone,tablet, smartwatch, Echo™ device, Alexa™ device, cable box, or othermobile communication device or smart device configured to be held,coupled to, or in proximity to the patient, that communicates with theTSS 10 by Bluetooth® low-energy (BLE) or WiFi®, or another electronichandshake such that acoustic information may be relayed to thecontroller 26 for real-time processing. In another embodiment, thecontroller 26 may be sized and configured to be embedded within thehousing 12 of the TSS 10. The controller 26 may further includeprocessing circuitry 25 with one or more processors to process the datareceived from the TSS 10. In one or more embodiments, the processingcircuitry 25 may include a processor 29 and a memory 31. In particular,in addition to or instead of a processor, such as a central processingunit, and memory, the processing circuitry 25 may comprise integratedcircuitry for processing and/or control, e.g., one or more processorsand/or processor cores and/or FPGAs (Field Programmable Gate Array)and/or ASICs (Application Specific Integrated Circuitry) adapted toexecute instructions. The processor 29 may be configured to access(e.g., write to and/or read from) the memory 31 which may comprise anykind of volatile and/or nonvolatile memory, e.g., cache and/or buffermemory and/or RAM (Random Access Memory) and/or ROM (Read-Only Memory)and/or optical memory and/or EPROM (Erasable Programmable Read-OnlyMemory). The processing circuitry 25 may be configured to control any ofthe methods and/or processes described herein and/or to cause suchmethods, and/or processes to be performed, e.g., by the controller 26.Processor 29 corresponds to one or more processors 29 for performingfunctions described herein. The memory 31 is configured to store data,programmatic software code and/or other information described herein. Insome embodiments, the software may include instructions that, whenexecuted by the processor 29 and/or processing circuitry 25 causes theprocessor 29 and/or processing circuitry 25 to perform the processesdescribed herein with respect to remote controller 26. For example,processing circuitry 25 of the remote controller 26 may include acontrol unit 33 that is configured to perform one or more functionsdescribed herein.

The results of such processing may be displayed on the display of thecontroller 26 or transmitted by the controller 26 to a remote locationfor further processing and/or analysis. As described herein, the AVMS 27of the present invention is also capable of performing the operations asset forth in U.S. application Ser. No. 17/308,084, filed on May 5, 2021,and entitled “ACOUSTIC SENSOR AND VENTILATION MONITORING SYSTEM,” andU.S. Pat. No. 11,000,212, issued on May 11, 2021, and entitled “ACOUSTICSENSOR AND VENTILATION MONITORING SYSTEM,” which are incorporated hereinby reference.

The wireless transmitter 24 and the sound transducer 20 may be poweredby a same rechargeable power source 28 such as, for example, arechargeable battery. Although the power source 28 is shown in FIGS. 1-6as being smaller size wise relative to some other components of TSS 10disclosed herein, it is noted that the illustrated size of the powersource 28 is merely exemplary and may be any shape or size. In oneembodiment (not shown), the TSS 10 may be recharged within a dedicatedhousing unit that includes a rechargeable power source. When in thededicated housing unit, the TSS 10 may be in electrical communicationwith the rechargeable power source such that TSS 10 may be rechargeableusing inductive coupling or wired connection via a cable to a UniversalSerial Bus (USB) port. A battery of the TSS 10 that lasts up to five ormore days may be disposable. However, the battery of the TSS 10 may lastfor a longer and/or a shorter period of time as well.

As shown in FIGS. 1-5 , the TSS 10 may include an adjustable elasticband or adhesive 30 adhered to the patient's skin proximate one of thetracheal notch or a lateral neck region of the patient to measure soundand/or vibrations associated with the patient's breathing. The adhesive30 may also at least partially surround the opening 18. The adhesive 30may be a double-sided tape or pad or other removable adhesive whichallows the TSS 10 to be releasably adhered to the skin of the patientafter remaining affixed to the patient for a predetermined period oftime, for example, 1 hour-14 days. In one configuration, the adhesive 30surrounds the opening 18 on the surface of the housing 12 withoutoccluding or otherwise blocking the opening 18 to avoid interfering withsound waves entering the chamber 14. When in contact with the skinsurface, the adhesive 30 provides an airtight seal for enhanced passivenoise suppression from ambient sounds. The TSS 10 may further include anaccelerometer 32, a temperature sensor 34, and/or a reflectance pulseoximeter 36, which may be positioned within the housing 12 and coupledto the power source 28 in communication with the controller 26. The3-axis accelerometer 32 may be configured to measure a relative x-y-zposition and a movement of the patient, such as the amount and patternof head bobbing, body movement, body coordination, and body position inreal-time to further estimate, in the case of, for example, a drugoverdose, the degree of sedation and the trends of sedation over time.The accelerometer 32 also senses chest wall movement to monitor theonset/timing of inhalation and exhalation. The temperature sensor 34 maybe integrated within the housing and used to detect a decrease orincrease in body temperature. The reflectance pulse oximeter 36 may beconfigured to monitor percent hemoglobin oxygen saturation and thephotoplethysmograph waveform, whether continuously, intermittently, orwhen the algorithm detects/predicts the onset of hypoventilation or achange in health. The pulse oximeter's waveform can be analyzed inreal-time to estimate heart rate, heart rate variability, stroke volume,stroke volume variability, pre-load, myocardial contractility, systemicvascular resistance, cardiac output, and systemic blood pressure. In oneconfiguration, at least a portion of the housing 12 may define aperimeter that is adjacent to and in contact with the temperature sensor34, the accelerometer 32, the at least one sound transducer 20, and theadhesive 30.

Referring now to FIG. 5 , in another configuration, the sound transducer20 may include a vibration sensor (electric, piezoelectric, or MEMS)configured to measure vibrations as a result of air flowing into and outof the trachea or lungs. The sound transducer 20 may be substantiallyplanar with the skin of the patient to increase mechanical coupling andsensitivity. The vibration sensor accelerometer 32 and the power source28 may be integrated into the housing 12. For example, a MEMS device maybe integrated within a first chamber 38 of the housing 12 separated fromthe sound transducer 20. The MEMS device may further be configured toprocess information from one or more of the sensors disclosed hereinwhich may be included in this configuration. The MEMS device may beincluded in any of the embodiments discussed above.

Referring now to FIG. 7 , as discussed above, the controller 26 isconfigured to perform a method of assigning a fitness levelclassification to the user based on the respiratory parameters measuredby the TSS 10. Primarily, the fitness level classification of the useris based on a comparison of the user's respiratory rate to a secondcalculated respiratory rate that is indicative of a respiratory rate ofa trained athlete as similarly disclosed in Naranjo, J, et al. “ANomogram for Assessment of Breathing Patterns during TreadmillExercise.” British Journal of Sports Medicine, vol. 39, no. 2, 2005, pp.80-83., doi:10.1136/bjsm.2003.009316. This allows users wearing the TSS10 to compare their respiratory parameters before, during, or afterexercise, an athletic or fitness performance test, or any other form ofphysical activity, to estimated respiratory parameters of a trainedathlete, and track their personal progress and improvement over time.

The method includes continuously, intermittently, and/or continuallymeasuring the RR and TV of the user wearing the TSS 10 in real-timebefore, during, or after exercise, an athletic or fitness performancetest, or any other form of physical activity (S700). In one embodiment,the TSS 10 and controller 26 also measure the user's heart rate,activity level, body position, body coordination, and body temperature.In one embodiment, once the user's RR and TV have been measured andtransmitted to the controller 26 (e.g., the user's smart watch), asecond calculated RR (RR2) value is calculated (S702) by the controller26 and the controller 26 may use the following equations:Men: RR2=8.3465e^(0.7458(TV))Women: RR2=9.6446e^(0.9328(TV))As shown above, “8.3465” and “9.6446” are exemplary values that areindicative of the correlation coefficients between tidal volume (TV) andbreathing frequency (BF) for men and women based on the type of exercisebeing performed. “0.7458” and “0.9328” are exemplary values indicativeof the relation between the ratio of TV to inspiratory time andventilation, for men and women. It is to be understood that equationsshown above are not limited to the specific numeric variables providedtherein. Rather, the equations may include any numeric values thatrepresent the respective correlation coefficients between TV and BF, andthe relation between the ratio of TV to inspiratory time andventilation.

Once RR2 has been calculated, the controller 26 then calculates abreathing efficiency (BE) ratio by comparing the RR2 value and theuser's RR (S704). As described herein, breathing efficiency may be anindicator of the user's respiratory efficiency or respiratory fitnesswhen compared to estimated respiratory parameters of, for example, atrained athlete. Respiratory function (how efficiency and effective aperson's breathing rate and depth are in providing needed oxygen totheir muscles and organs) is a key indicator of physical fitness andhealth. The user's BE ratio provides the user with an indication andcomparison of how efficient and effective their respiratory function iswhen compared to an average trained athlete—someone who is capable ofperforming at a high level of physical activity.

Once the BE ratio has been calculated, the controller 26 then comparesthe ratio to a predefined threshold value or range (as shown in TABLE 1below) to determine a classification that should be assigned to the user(S706). The threshold “1.0” is an exemplary value representative of theaverage breathing efficiency of a trained athlete. The threshold valueis determined by calculating the average breathing efficiency before,during, or after exercise, an athletic or fitness performance test, orany other monitored form of physical activity, from a sample pool oftrained professional and/or amateur athletes. If the calculated BE ratioof the user is equal to 1.0, then the user using the TSS 10 has arespiratory function performance (i.e., respiratory efficiency)substantially equivalent to the average BE of trained athletes. If thecalculated BE ratio is less than 1.0, the user has a respiratoryfunction performance which is less efficient than an average trainedathlete. If the calculated BE ratio is greater than 1.0, the user has arespiratory function performance that is greater than an average trainedathlete. In one configuration, based on the user's BE ratio, thecontroller 26 may assign the user one of the following classifications:elite athlete level (BE>1.0), trained athlete level (BE=1.0), and lesserathlete level (BE<1.0) (S708). Once the user's classification has beendetermined by the controller 26, the controller 26 may display theclassification for the user or transmit a signal to an external displayfor visualization by the user (S710).

TABLE 1 Breathing Efficiency Classifications BE Ratio PerformanceClassification BE > 1.0 Elite Athlete Level BE = 1.0 Average TrainedAthlete Level BE < 1.0 Lesser Athlete Level

It will be understood that as described herein, the present embodimentsare not limited to the aforementioned classification terminology.Rather, in alternative embodiments, the controller 26 may assign anyclassification that is indicative of the user's respiratory efficiencylevel when compared to estimated respiratory parameters of an averagetrained athlete. The controller 26 is not limited to assigning only anelite athlete level, a trained athlete level, or a lesser athlete levelto the user.

As used herein, relational terms, such as “first” and “second,” “top”and “bottom,” and the like, may be used solely to distinguish one entityor element from another entity or element without necessarily requiringor implying any physical or logical relationship or order between suchentities or elements. The terminology used herein is for the purpose ofdescribing particular embodiments only and is not intended to belimiting of the concepts described herein. As used herein, the singularforms “a”, “an” and “the” are intended to include the plural forms aswell, unless the context clearly indicates otherwise. It will be furtherunderstood that the terms “comprises,” “comprising,” “includes” and/or“including” when used herein, specify the presence of stated features,integers, steps, operations, elements, and/or components, but do notpreclude the presence or addition of one or more other features,integers, steps, operations, elements, components, and/or groupsthereof.

Unless otherwise defined, all terms (including technical and scientificterms) used herein have the same meaning as commonly understood by oneof ordinary skill in the art to which this disclosure belongs. It willbe further understood that terms used herein should be interpreted ashaving a meaning that is consistent with their meaning in the context ofthis specification and the relevant art and will not be interpreted inan idealized or overly formal sense unless expressly so defined herein.

In embodiments described herein, the joining term, “in communicationwith” and the like, may be used to indicate electrical or datacommunication, which may be accomplished by physical contact, induction,electromagnetic radiation, radio signaling, infrared signaling oroptical signaling, for example. One having ordinary skill in the artwill appreciate that multiple components may interoperate, and thatmodifications and variations are possible of achieving the electricaland data communication.

In one or more examples, the described techniques may be implemented inhardware, software, firmware, or any combination thereof. If implementedin software, the functions may be stored as one or more instructions orcode on a computer-readable medium and executed by a hardware-basedprocessing unit. Computer-readable media may include non-transitorycomputer-readable media, which corresponds to a tangible medium such asdata storage media (e.g., RAM, ROM, EEPROM, flash memory, or any othermedium that can be used to store desired program code in the form ofinstructions or data structures that can be accessed by a computer).

Instructions may be executed by one or more processors, such as one ormore digital signal processors (DSPs), general purpose microprocessors,application specific integrated circuits (ASICs), field programmablelogic arrays (FPLAs), or other equivalent integrated or discrete logiccircuitry. Accordingly, the term “processor” as used herein may refer toany of the foregoing structure or any other physical structure suitablefor implementation of the described techniques. Also, the techniquescould be fully implemented in one or more circuits or logic elements.

It will be appreciated by persons skilled in the art that the presentembodiments are not limited to what has been particularly shown anddescribed herein above. In addition, unless mention was made above tothe contrary, it should be noted that all of the accompanying drawingsare not to scale. A variety of modifications and variations are possiblein light of the above teachings.

The invention claimed is:
 1. A method of determining a fitness level ofa user with an acoustic measurement device the method comprising:measuring sound associated with airflow through a mammalian trachea, theacoustic measurement device including a housing and at least one soundtransducer wherein the at least one sound transducer is suspended in thehousing; correlating the measured sound into a measurement of the user'srespiratory rate and tidal volume; calculating a respiratory rate valueusing the measured tidal volume, the respiratory rate value beingcalculated using the measured tidal volume with a first equation for menand a second equation for women, the first equation beingRR2=8.3465e^(0.7458(tidal volume)) and the second equation beingRR2=9.6446e^(0.9328(tidal volume)); calculating a breathing efficiency(BE) ratio based on a comparison of the user's measured respiratory rateand the calculated respiratory rate value; correlating the calculated BEratio to a predetermined threshold; and assigning a classification tothe user based on the calculated BE ratio, the classification beingindicative of the user's respiratory function performance.
 2. The methodof claim 1, wherein the at least one sound transducer is removablyaffixed with the housing.
 3. The method of claim 1, wherein the assignedclassification is one selected from the group consisting of: an eliteathlete level; a trained athlete level; and a lesser athlete level. 4.The method of claim 3, wherein: the elite athlete level classificationis assigned when the BE ratio is greater than the predeterminedthreshold; the trained athlete level classification is assigned when theBE ratio is equal to the predetermined threshold; and the lesser athletelevel classification is assigned when the BE ratio is less than thepredetermined threshold.
 5. The method of claim 4, wherein the eliteathlete level has a BE>1.0, the trained athlete level has a BE=1.0, andthe lesser athlete level has a BE<1.0.
 6. The method of claim 1, whereinthe measurement of sound associated with airflow through the tracheaoccurs at least one from the group consisting of periodically,intermittently, and continuously.
 7. The method of claim 1, wherein theat least one sound transducer has a vibration sensor.
 8. The method ofclaim 7, wherein the housing of the acoustic measurement device has awidth between 0.5 cm and 3.5 cm.
 9. The method of claim 1, wherein theacoustic measurement device has a controller, the acoustic measurementdevice being in wireless communication with the controller.
 10. Themethod of claim 9, wherein the controller is a smart device.
 11. Themethod of claim 1, further comprising filtering out a set of anomalousdata and ambient noise from the measured sound.
 12. A method ofdetermining a fitness level of a user with an acoustic measurementdevice at least one of before, during, or after physical activity, themethod comprising: measuring sound associated with airflow through amammalian trachea, the acoustic measurement device including a housingand at least one sound transducer wherein the at least one soundtransducer is suspended in the housing; correlating the measured soundinto a measurement of the user's respiratory rate and tidal volume at apredetermined time interval; calculating a respiratory rate value usingthe measured tidal volume, the respiratory rate value being calculatedusing the measured tidal volume with a first equation for men and asecond equation for women, the first equation beingRR2=8.3465e^(0.7458(tidal volume)) and the second equation beingRR2=9.6446e^(0.9328(tidal volume)); calculating a breathing efficiency(BE) ratio based on a comparison of the user's measured respiratory rateand the calculated respiratory rate value; correlating the calculated BEratio to a predetermined threshold; and assigning a classification tothe user based on the calculated BE ratio, the classification being oneselected from the group consisting of: an elite athlete level; a trainedathlete level; and a lesser athlete level.
 13. The method of claim 12,wherein: the elite athlete level classification is assigned when the BEratio is greater than the predetermined threshold; the trained athletelevel classification is assigned when the BE ratio is equal to thepredetermined threshold; and the lesser athlete level classification isassigned when the BE ratio is less than the predetermined threshold. 14.The method of claim 12, wherein the measurement of sound associated withairflow through the trachea occurs at least one from the groupconsisting of periodically, intermittently, and continuously.
 15. Themethod of claim 12, wherein the housing of the acoustic measurementdevice has a width between 0.5 cm and 3.5 cm.
 16. The method of claim12, wherein the acoustic measurement device is in communication with acontroller, the controller being configured to correlate the measuredsound into the measurement of the user's respiratory rate and tidalvolume at a predetermined time interval, calculate the respiratory ratevalue using the measured tidal volume, calculate the breathingefficiency (BE) ratio based on the comparison of the user's measuredrespiratory rate and the second respiratory rate value, correlate thecalculated BE ratio to the predetermined threshold, and assign theclassification to the user based on the calculated BE ratio, theclassification being one selected from the group consisting of the eliteathlete level, the trained athlete level, and the lesser athlete level.17. The method of claim 16, wherein the controller is a smart device.18. The method of claim 12, further comprising filtering out a set ofanomalous data and ambient noise from the measured sound.
 19. The methodof claim 12, wherein the housing is configured to releasably couple toskin of the mammalian trachea by an adhesive or an adjustable band. 20.A method of determining a fitness level of a user with an acousticmeasurement device at least one of before, during, or after physicalactivity, the method comprising: measuring sound associated with airflowthrough a mammalian trachea, the acoustic measurement device including ahousing and at least one sound transducer wherein the at least one soundtransducer is suspended in the housing; correlating the measured soundinto a measurement of the user's respiratory rate and tidal volume at apredetermined time interval; calculating a respiratory rate value usingthe measured tidal volume, the respiratory rate value being calculatedusing the measured tidal volume with a first equation for men and asecond equation for women, the first equation beingRR2=8.3465e^(0.7458(tidal volume)) and the second equation beingRR2=9.6446e^(0.9328(tidal volume)); calculating a breathing efficiency(BE) ratio based on a comparison of the user's measured respiratory rateand the calculated respiratory rate value; for a predetermined point intime or over a predetermined period of time; correlating the calculatedBE ratio to a predetermined threshold; and assigning a classification tothe user based on the calculated BE ratio, the classification being oneselected from the group consisting of: an elite athlete level where thisclassification is assigned when the BE ratio is greater than thepredetermined threshold; a trained athlete level where thisclassification is assigned when the BE ratio is equal to thepredetermined threshold; and a lesser athlete level where thisclassification is assigned when the BE ratio is less than thepredetermined threshold.